Continuous Fiber Optic Functionality Monitoring and Self-Diagnostic Reporting System

ABSTRACT

A system, apparatus and method directed to detecting damage to an optical fiber of a medical device. The optical fiber includes one or more core fibers each including a plurality of sensors configured to (i) reflect a light signal based on received incident light, and (ii) alter the reflected light signal for use in determining a physical state of the multi-core optical fiber. The system also includes a console having non-transitory computer-readable medium storing logic that, when executed, causes operations of providing a broadband incident light signal to the multi-core optical fiber, receiving reflected light signals, receiving reflected light signals of different spectral widths of the broadband incident light by one or more of the plurality of sensors, identifying at least one unexpected spectral width or a lack of an expected spectral width, and determining the damage has occurred to the optical fiber based on the identification.

PRIORITY

This application is a division of U.S. patent application Ser. No. 17/371,993, filed Jul. 9, 2021, now U.S. Pat. No. 11,624,677, which claims the benefit of priority to U.S. Provisional Application No. 63/050,641, filed Jul. 10, 2020, each of which is incorporated by reference in its entirety into this application.

BACKGROUND

In the past, certain intravascular guidance of medical devices, such as guidewires and catheters for example, have used fluoroscopic methods for tracking tips of the medical devices and determining whether distal tips are appropriately localized in their target anatomical structures. However, such fluoroscopic methods expose patients and their attending clinicians to harmful X-ray radiation. Moreover, in some cases, the patients are exposed to potentially harmful contrast media needed for the fluoroscopic methods.

More recently, electromagnetic tracking systems have been used involving stylets. Generally, electromagnetic tracking systems feature three components: a field generator, a sensor unit and control unit. The field generator uses several coils to generate a position-varying magnetic field, which is used to establish a coordinate space. Attached to the stylet, such as near a distal end (tip) of the stylet for example, the sensor unit includes small coils in which current is induced via the magnetic field. Based on the electrical properties of each coil, the position and orientation of the medical device may be determined within the coordinate space. The control unit controls the field generator and captures data from the sensor unit.

Although electromagnetic tracking systems avoid line-of-sight reliance in tracking the tip of a stylet while obviating radiation exposure and potentially harmful contrast media associated with fluoroscopic methods, electromagnetic tracking systems are prone to interference. More specifically, since electromagnetic tracking systems depend on the measurement of magnetic fields produced by the field generator, these systems are subject to electromagnetic field interference, which may be caused by the presence of many different types of consumer electronics such as cellular telephones. Additionally, electromagnetic tracking systems are subject to signal drop out, depend on an external sensor, and are defined to a limited depth range.

Disclosed herein is a fiber optic shape sensing system and methods performed thereby where the system is configured to provide confirmation of tip placement or tracking information using optical fiber technology. Further, the system is configured to detect damage to one or more core fibers and, optionally, a location of the damage along the core fiber(s). Some embodiments combine the fiber optic shape sensing functionality with one or more of intravascular electrocardiogram (ECG) monitoring, impedance/conductance sensing and blood flow directional detection.

SUMMARY

Briefly summarized, embodiments disclosed herein are directed to systems, apparatus and methods for obtaining three-dimensional (3D) information (reflected light) corresponding to a trajectory and/or shape of a medical instrument, such as a catheter, a guidewire, or a stylet, via a fiber optic core during advancement through a vasculature of a patient, monitoring a health of the fiber optic core, and determining when a kink or damage has occurred to the fiber optic core.

More particularly, in some embodiments, the medical instrument includes core optical fiber core configured with an array of sensors (reflective gratings), which are spatially distributed over a prescribed length of the core fiber to generally sense external strain on those regions of the core fiber occupied by the sensor. The optical fiber core is configured to receive broadband light from a console during advancement through the vasculature of a patient, where the broadband light propagates along at least a partial distance of the optical fiber core toward the distal end. Given that each sensor positioned along the optical fiber core is configured to reflect light of a different, specific spectral width, the array of sensors enables distributed measurements throughout the prescribed length of the multi-core optical fiber. These distributed measurements may include wavelength shifts having a correlation with strain experienced by the sensor.

The reflected light from the sensors (reflective gratings) within the optical fiber core is returned from the medical instrument for processing by the console. The physical state of the medical instrument may be ascertained based on analytics of the wavelength shifts of the reflected light. For example, the strain caused through bending of the medical instrument, and hence angular modification of the optical fiber core, causes different degrees of deformation. The different degrees of deformation alter the shape of the sensors (reflective grating) positioned on the optical fiber core, which may cause variations (shifts) in the wavelength of the reflected light from the sensors positioned on the optical fiber core. The optical fiber core may comprise a single optical fiber, or a plurality of optical fibers (in which case, the optical fiber core is referred to as a “multi-core optical fiber”).

As used herein, the term “core fiber,” generally refers to a single optical fiber core disposed within a medical device. Thus, discussion of a core fiber refers to single optical fiber core and discussion of a multi-core optical fiber refers to a plurality of core fibers. Various embodiments discussed below to detection of the health (and particularly the damage) that occurs in each of an optical fiber core of medical device including (i) a single core fiber, and (ii) a plurality of core fibers.

Specific embodiments of the disclosure include utilization of a medical instrument, such as a stylet, featuring a multi-core optical fiber and a conductive medium that collectively operate for tracking placement with a body of a patient of the stylet or another medical device (such as a catheter) in which the stylet is disposed. In lieu of a stylet, a guidewire may be utilized. For convenience, embodiments are generally discussed where the optical fiber core is disposed within a stylet; however, the disclosure is not intended to be so limited as the functionality involving detection of the health of an optical fiber core disclosed herein may be implemented regardless of the medical device in which the optical fiber core is disposed.

In some embodiments, the optical fiber core of a stylet is configured to return information for use in identifying its physical state (e.g., shape length, shape, and/or form) of (i) a portion of the stylet (e.g., tip, segment of stylet, etc.) or a portion of a catheter inclusive of at least a portion of the stylet (e.g., tip, segment of catheter, etc.) or (ii) the entirety or a substantial portion of the stylet or catheter within the body of a patient (hereinafter, described as the “physical state of the stylet” or the “physical state of the catheter”). According to one embodiment of the disclosure, the returned information may be obtained from reflected light signals of different spectral widths, where each reflected light signal corresponds to a portion of broadband incident light propagating along a core of the multi-core optical fiber (hereinafter, “core fiber”) that is reflected back over the core fiber by a particular sensor located on the core fiber. One illustrative example of the returned information may pertain to a change in signal characteristics of the reflected light signal returned from the sensor, where wavelength shift is correlated to (mechanical) strain on the core fiber.

In some embodiments, the core fiber utilizes a plurality of sensors and each sensor is configured to reflect a different spectral range of the incident light (e.g., different light frequency range). Based on the type and degree of strain asserted on each core fiber, the sensors associated with that core fiber may alter (shift) the wavelength of the reflected light to convey the type and degree of stain on that core fiber at those locations of the stylet occupied by the sensors. The sensors are spatially distributed at various locations of the core fiber between a proximal end and a distal end of the stylet so that shape sensing of the stylet may be conducted based on analytics of the wavelength shifts. Herein, the shape sensing functionality is paired with the ability to simultaneously pass an electrical signal through the same member (stylet) through conductive medium included as part of the stylet.

More specifically, in some embodiments each core fiber of the multi-core optical fiber is configured with an array of sensors, which are spatially distributed over a prescribed length of the core fiber to generally sense external strain those regions of the core fiber occupied by the sensor. Given that each sensor positioned along the same core fiber is configured to reflect light of a different, specific spectral width, the array of sensors enables distributed measurements throughout the prescribed length of the multi-core optical fiber. These distributed measurements may include wavelength shifts having a correlation with strain experienced by the sensor.

According to one embodiment of the disclosure, each sensor may operate as a reflective grating such as a fiber Bragg grating (FBG), namely an intrinsic sensor corresponding to a permanent, periodic refractive index change inscribed into the core fiber. Stated differently, the sensor operates as a light reflective mirror for a specific spectral width (e.g., a specific wavelength or specific range of wavelengths). As a result, as broadband incident light is supplied by an optical light source and propagates through a particular core fiber, upon reaching a first sensor of the distributed array of sensors for that core fiber, light of a prescribed spectral width associated with the first sensor is reflected back to an optical receiver within a console, including a display and the optical light source. The remaining spectrum of the incident light continues propagation through the core fiber toward a distal end of the stylet. The remaining spectrum of the incident light may encounter other sensors from the distributed array of sensors, where each of these sensors is fabricated to reflect light with different specific spectral widths to provide distributed measurements, as described above.

During operation, multiple light reflections (also referred to as “reflected light signals”) are returned to the console from each of the plurality of core fibers of the multi-core optical fiber. Each reflected light signal may be uniquely associated with a different spectral width. Information associated with the reflected light signals may be used to determine a three-dimensional representation of the physical state of the stylet within the body of a patient. Herein, the core fibers are spatially separated with the cladding of the multi-mode optical fiber and each core fiber is configured to separately return light of different spectral widths (e.g., specific light wavelength or a range of light wavelengths) reflected from the distributed array of sensors fabricated in each of the core fibers. A comparison of detected shifts in wavelength of the reflected light returned by a center core fiber (operating as a reference) and the surrounding, periphery core fibers may be used to determine the physical state of the stylet.

During vasculature insertion and advancement of the catheter, the clinician may rely on the console to visualize a current physical state (e.g., shape) of a catheter guided by the stylet to avoid potential path deviations. As the periphery core fibers reside at spatially different locations within the cladding of the multi-mode optical fiber, changes in angular orientation (such as bending with respect to the center core fiber, etc.) of the stylet imposes different types (e.g., compression or tension) and degrees of strain on each of the periphery core fibers as well as the center core fiber. The different types and/or degree of strain may cause the sensors of the core fibers to apply different wavelength shifts, which can be measured to extrapolate the physical state of the stylet (catheter).

Embodiments of the disclosure may include a combination of one or more of the methodologies to determine when an optical fiber within a body of implementation (e.g., an introducer wire, a guidewire, a stylet within a needle, a needle with fiber optic inlayed into the cannula, a stylet configured for use with a catheter, an optical fiber between a needle and a catheter, and/or an optical fiber integrated into a catheter) has incurred damage and/or been kinked such that a portion of the optical fiber is non-functional (i.e., unable to provide accurate, uncorrupted reflected light signals back to a console).

Certain embodiments of the disclosure pertain to the utilization of fiber optic shape sensing to track advancement of a body of implementation throughout the vasculature of a patient and detecting damage to one or more core fibers of the optical fiber integrated into the body of implementation. For example, as noted above, each core fiber includes a plurality of reflective gratings disposed along its length, wherein each reflective grating receives broadband incident light and reflects light signals having a specific spectral width (e.g., a specific wavelength or specific range of wavelengths) that may be shifted based on an amount of strain applied to a length of the core fiber corresponding to the reflective grating. Detection of damage to a core fiber is performed through an analysis of the received reflected light signals and, specifically, identification of reflective gratings from which a corrupted or degraded reflected light signal was received, a reflected light signal was received having a reduced intensity (e.g., power transferred per unit area) or a reflected light signal was not received.

Further, some embodiments include analysis of the specific spectral width of each received reflected light signal to determine a location along the core fiber at which damage (or a kink) occurred. Specifically, logic of the console determines from which core fiber each reflected light signal was received and further analyzes the specific spectral width of each received reflected light signal to identify (i) a most distal reflective grating from which a normal, uncorrupted light signal was received, and a (ii) a most proximal reflective grating from which a corrupted (e.g., degraded) light signal was received. Such an identification of reflective gratings results in an identification of the location of the kink or point of damage.

Further embodiments of the disclosure pertain to the use of fiber optic shape sensing to identify damage to a core fiber and the location thereof as well as to detect fluctuation of the body of implementation. For example, deviation of the advancement of the body of implementation out of the SVC into the Azygos vein is identified via a reduction in fluctuations in the body of implementation. Additionally, intravascular ECG monitoring may be combined with either or both of the fiber optic shape sensing methodologies referenced above to detect deviation of the advancement of the body of implementation into the Azygos vein as the detected P-wave of the intravascular ECG decreases in slightly in amplitude even as the body of implementation is advanced towards the sinoatrial (SA) node. Additionally, or in the alternative, impedance/conductance sensing may be combined with either or both of the fiber optic shape sensing methodologies and, optionally, the ECG intravascular ECG monitoring to detect deviation of the advancement of the body of implementation into the Azygos vein. For instance, as the body of implementation deviates into the Azygos vein the smaller diameter vessel is characterized by a varied impedance/conductance.

In yet other embodiments, the direction of the blood flow may be utilized in combination with any of the fiber optic shape sensing methodologies, intravascular ECG monitoring and/or impedance/conductance sensing referenced above. For instance, as the body of implementation deviates into the Azygos vein, the flow of blood will change from in-line with the advancement of the body of implementation to against the advancement of the body of implementation, which may be detected using pulse oximetry and/or blood flow Doppler.

Some embodiments include a medical device system for detecting damage to a optical fiber technology of a medical device, where the system comprises the medical device including an optical fiber having one or more of core fibers, each of the one or more core fibers including a plurality of sensors distributed along a longitudinal length of a corresponding core fiber and each sensor of the plurality of sensors being configured to (i) reflect a light signal of a different spectral width based on received incident light, and (ii) change a characteristic of the reflected light signal for use in determining a physical state of the optical fiber. The system may also include a console including one or more processors and a non-transitory computer-readable medium having stored thereon logic, when executed by the one or more processors, causes operations including providing a broadband incident light signal to the optical fiber, receiving reflected light signals of different spectral widths of the broadband incident light by one or more of the plurality of sensors, processing the reflected light signals associated with the one or more of core fibers to identify at least one unexpected spectral width or a lack of an expected spectral width, and determining the damage has occurred to one or more of the core fibers based on identification of the at least one unexpected spectral width or the lack of an expected spectral width.

In some embodiments, an unexpected spectral width is a spectral width not configured for use by any of the plurality of sensors of a core fiber. In some embodiments, the optical fiber is a single-core optical fiber. In other embodiments, the optical fiber is a multi-core optical fiber including a plurality of core fibers. In some embodiments, the damage affects a first subset of the plurality of core-fibers.

In some embodiments, a second subset of the plurality of core fibers is unaffected by the damage such that multi-core optical fiber maintains at least partial functionality based on the second subset of the plurality of core-fibers. In some embodiments, the at least partial functionality includes one or more of fluctuation sensing of a distal tip of the medical device, shape sensing of the multi-core optical fiber, oximetry monitoring, distal tip confirmation, distal tip location detection, detection of entry of the distal tip of the medical device into an Azygos vein, impedance or conductance sensing, intravascular ECG monitoring or vessel cannulation detection.

In further embodiments, the logic, when executed by the one or more processors, causes further operations including performing at least partial functionality of the multi-core optical fiber without considering information provided by a first core fiber that has reflected a light signal having a first unexpected wavelength. In some embodiments, the second subset of the plurality of core fibers includes redundant core fibers such that a shape sensing functionality of the multi-core optical fiber is maintained. In yet other embodiments, the medical device is one of an introducer wire, a guidewire, a stylet, a stylet within a needle, a needle with the optical fiber inlayed into a cannula of the needle or a catheter with the optical fiber inlayed into one or more walls of the catheter.

In some embodiments, the logic, when executed by the one or more processors, causes further operations including determining a first core fiber affected by the damage, and determining a location of the damage along the first core fiber. In some embodiments, determining the first core fiber is based on a unique identifier assigned to the first core fiber and association of unique identifier with each light signal reflected by the first core fiber. In some embodiments, determining the location of the damage includes identifying (i) a most distal sensor of the first core fiber from which a first light signal having an expected spectral width was received, and a (ii) a most proximal sensor from which a second light signal having a first unexpected spectral width was received, second light signal having a reduction in intensity was received or a corresponding expected spectral width was not received. In yet further embodiments, each of the plurality of sensors is a reflective grating, where each reflective grating alters its reflected light signal by applying a wavelength shift dependent on a strain experienced by the reflective grating.

Some embodiments include a method for placing a medical device into a body of a patient, the method comprising certain operations including providing a broadband incident light signal to an optical fiber included within the medical device, wherein the optical fiber includes a one or more of core fibers, each of the one or more of core fibers including a plurality of reflective gratings distributed along a longitudinal length of a corresponding core fiber and each of the plurality of reflective gratings being configured to (i) reflect a light signal of a different spectral width based on received incident light, and (ii) change a characteristic of the reflected light signal for use in determining a physical state of the optical fiber and receiving reflected light signals of different spectral widths of the broadband incident light by one or more of the plurality of sensors. The operations further include processing the reflected light signals associated with the one or more of core fibers to identify at least one unexpected spectral width or a lack of an expected spectral width, and determining the damage has occurred to one or more of the core fibers based on identification of the at least one unexpected spectral width or the lack of an expected spectral width.

In some embodiments, an unexpected spectral width is a spectral width not configured for use by any of the plurality of sensors of a core fiber. In some embodiments, the optical fiber is a single-core optical fiber. In other embodiments, the optical fiber is a multi-core optical fiber including a plurality of core fibers. In some embodiments, the damage affects a first subset of the plurality of core-fibers.

In some embodiments, a second subset of the plurality of core fibers is unaffected by the damage such that multi-core optical fiber maintains at least partial functionality based on the second subset of the plurality of core-fibers. In some embodiments, the at least partial functionality includes one or more of fluctuation sensing of a distal tip of the medical device, shape sensing of the multi-core optical fiber, oximetry monitoring, distal tip confirmation, distal tip location detection, detection of entry of the distal tip of the medical device into an Azygos vein, impedance or conductance sensing, intravascular ECG monitoring or vessel cannulation detection.

In further embodiments, the logic, when executed by the one or more processors, causes further operations including performing at least partial functionality of the multi-core optical fiber without considering information provided by a first core fiber that has reflected a light signal having a first unexpected wavelength. In some embodiments, the second subset of the plurality of core fibers includes redundant core fibers such that a shape sensing functionality of the multi-core optical fiber is maintained. In yet other embodiments, the medical device is one of an introducer wire, a guidewire, a stylet, a stylet within a needle, a needle with the optical fiber inlayed into a cannula of the needle or a catheter with the optical fiber inlayed into one or more walls of the catheter.

In some embodiments, the logic, when executed by the one or more processors, causes further operations including determining a first core fiber affected by the damage, and determining a location of the damage along the first core fiber. In some embodiments, determining the first core fiber is based on a unique identifier assigned to the first core fiber and association of unique identifier with each light signal reflected by the first core fiber. In some embodiments, determining the location of the damage includes identifying (i) a most distal sensor of the first core fiber from which a first light signal having an expected wavelength was received, and a (ii) a most proximal sensor from which a second light signal having a first unexpected spectral width was received, second light signal having a reduction in intensity was received or a corresponding expected spectral width was not received. In yet further embodiments, each of the plurality of sensors is a reflective grating, where each reflective grating alters its reflected light signal by applying a wavelength shift dependent on a strain experienced by the reflective grating.

Some embodiments disclose a non-transitory computer-readable medium having stored thereon logic that, when executed by the one or more processors, causes operations including providing a broadband incident light signal to an optical fiber included within the medical device, wherein the optical fiber includes a one or more of core fibers, each of the one or more of core fibers including a plurality of reflective gratings distributed along a longitudinal length of a corresponding core fiber and each of the plurality of reflective gratings being configured to (i) reflect a light signal of a different spectral width based on received incident light, and (ii) change a characteristic of the reflected light signal for use in determining a physical state of the optical fiber and receiving reflected light signals of different spectral widths of the broadband incident light by one or more of the plurality of sensors. The operations further include processing the reflected light signals associated with the one or more of core fibers to identify at least one unexpected spectral width or a lack of an expected spectral width, and determining the damage has occurred to one or more of the core fibers based on identification of the at least one unexpected spectral width or the lack of an expected spectral width.

In some embodiments, an unexpected spectral width is a spectral width not configured for use by any of the plurality of sensors of a core fiber. In some embodiments, the optical fiber is a single-core optical fiber. In other embodiments, the optical fiber is a multi-core optical fiber including a plurality of core fibers. In some embodiments, the damage affects a first subset of the plurality of core-fibers.

In some embodiments, a second subset of the plurality of core fibers is unaffected by the damage such that multi-core optical fiber maintains at least partial functionality based on the second subset of the plurality of core-fibers. In some embodiments, the at least partial functionality includes one or more of fluctuation sensing of a distal tip of the medical device, shape sensing of the multi-core optical fiber, oximetry monitoring, distal tip confirmation, distal tip location detection, detection of entry of the distal tip of the medical device into an Azygos vein, impedance or conductance sensing, intravascular ECG monitoring or vessel cannulation detection.

In further embodiments, the logic, when executed by the one or more processors, causes further operations including performing at least partial functionality of the multi-core optical fiber without considering information provided by a first core fiber that has reflected a light signal having a first unexpected wavelength. In some embodiments, the second subset of the plurality of core fibers includes redundant core fibers such that a shape sensing functionality of the multi-core optical fiber is maintained. In yet other embodiments, the medical device is one of an introducer wire, a guidewire, a stylet, a stylet within a needle, a needle with the optical fiber inlayed into a cannula of the needle or a catheter with the optical fiber inlayed into one or more walls of the catheter.

In some embodiments, the logic, when executed by the one or more processors, causes further operations including determining a first core fiber affected by the damage, and determining a location of the damage along the first core fiber. In some embodiments, determining the first core fiber is based on a unique identifier assigned to the first core fiber and association of unique identifier with each light signal reflected by the first core fiber. In some embodiments, determining the location of the damage includes identifying (i) a most distal sensor of the first core fiber from which a first light signal having an expected wavelength was received, and a (ii) a most proximal sensor from which a second light signal having a first unexpected spectral width was received, second light signal having a reduction in intensity was received or a corresponding expected spectral width was not received. In yet further embodiments, each of the plurality of sensors is a reflective grating, where each reflective grating alters its reflected light signal by applying a wavelength shift dependent on a strain experienced by the reflective grating.

These and other features of the concepts provided herein will become more apparent to those of skill in the art in view of the accompanying drawings and following description, which disclose particular embodiments of such concepts in greater detail.

BRIEF DESCRIPTION OF THE DRAWINGS

Embodiments of the disclosure are illustrated by way of example and not by way of limitation in the figures of the accompanying drawings, in which like references indicate similar elements and in which:

FIG. 1A is an illustrative embodiment of a medical instrument monitoring system including a medical instrument with optic shape sensing and fiber optic-based oximetry capabilities in accordance with some embodiments;

FIG. 1B is an alternative illustrative embodiment of the medical instrument monitoring system 100 in accordance with some embodiments;

FIG. 2 is an exemplary embodiment of a structure of a section of the multi-core optical fiber included within the stylet 120 of FIG. 1A in accordance with some embodiments;

FIG. 3A is a first exemplary embodiment of the stylet of FIG. 1A supporting both an optical and electrical signaling in accordance with some embodiments;

FIG. 3B is a cross sectional view of the stylet of FIG. 3A in accordance with some embodiments;

FIG. 4A is a second exemplary embodiment of the stylet of FIG. 1B in accordance with some embodiments;

FIG. 4B is a cross sectional view of the stylet of FIG. 4A in accordance with some embodiments;

FIG. 5A is an elevation view of a first illustrative embodiment of a catheter including integrated tubing, a diametrically disposed septum, and micro-lumens formed within the tubing and septum in accordance with some embodiments;

FIG. 5B is a perspective view of the first illustrative embodiment of the catheter of FIG. 5A including core fibers installed within the micro-lumens in accordance with some embodiments;

FIGS. 6A-6B are flowcharts of the methods of operations conducted by the medical instrument monitoring system of FIGS. 1A-1B to achieve optic 3D shape sensing in accordance with some embodiments;

FIG. 7 is an exemplary embodiment of the medical instrument monitoring system of FIG. 1A during operation and insertion of the catheter into a patient in accordance with some embodiments;

FIG. 8 is an embodiment of a structure of a section of a single core optical fiber included within the stylet 120 of FIG. 1A that is kinked or damaged in accordance with some embodiments;

FIG. 9A is an embodiment of a structure of a section of a multi-core optical fiber included within the stylet 120 of FIG. 1A that is kinked or partially damaged in accordance with some embodiments;

FIG. 9B is an embodiment of a structure of a section of a multi-core optical fiber included within the stylet 120 of FIG. 1A that is completely damaged in accordance with some embodiments.

DETAILED DESCRIPTION

Before some particular embodiments are disclosed in greater detail, it should be understood that the particular embodiments disclosed herein do not limit the scope of the concepts provided herein. It should also be understood that a particular embodiment disclosed herein can have features that can be readily separated from the particular embodiment and optionally combined with or substituted for features of any of a number of other embodiments disclosed herein.

Regarding terms used herein, it should also be understood the terms are for the purpose of describing some particular embodiments, and the terms do not limit the scope of the concepts provided herein. Ordinal numbers (e.g., first, second, third, etc.) are generally used to distinguish or identify different features or steps in a group of features or steps, and do not supply a serial or numerical limitation. For example, “first,” “second,” and “third” features or steps need not necessarily appear in that order, and the particular embodiments including such features or steps need not necessarily be limited to the three features or steps. Labels such as “left,” “right,” “top,” “bottom,” “front,” “back,” and the like are used for convenience and are not intended to imply, for example, any particular fixed location, orientation, or direction. Instead, such labels are used to reflect, for example, relative location, orientation, or directions. Singular forms of “a,” “an,” and “the” include plural references unless the context clearly dictates otherwise.

With respect to “proximal,” a “proximal portion” or a “proximal end portion” of, for example, a probe disclosed herein includes a portion of the probe intended to be near a clinician when the probe is used on a patient. Likewise, a “proximal length” of, for example, the probe includes a length of the probe intended to be near the clinician when the probe is used on the patient. A “proximal end” of, for example, the probe includes an end of the probe intended to be near the clinician when the probe is used on the patient. The proximal portion, the proximal end portion, or the proximal length of the probe can include the proximal end of the probe; however, the proximal portion, the proximal end portion, or the proximal length of the probe need not include the proximal end of the probe. That is, unless context suggests otherwise, the proximal portion, the proximal end portion, or the proximal length of the probe is not a terminal portion or terminal length of the probe.

With respect to “distal,” a “distal portion” or a “distal end portion” of, for example, a probe disclosed herein includes a portion of the probe intended to be near or in a patient when the probe is used on the patient. Likewise, a “distal length” of, for example, the probe includes a length of the probe intended to be near or in the patient when the probe is used on the patient. A “distal end” of, for example, the probe includes an end of the probe intended to be near or in the patient when the probe is used on the patient. The distal portion, the distal end portion, or the distal length of the probe can include the distal end of the probe; however, the distal portion, the distal end portion, or the distal length of the probe need not include the distal end of the probe. That is, unless context suggests otherwise, the distal portion, the distal end portion, or the distal length of the probe is not a terminal portion or terminal length of the probe.

The term “logic” may be representative of hardware, firmware or software that is configured to perform one or more functions. As hardware, the term logic may refer to or include circuitry having data processing and/or storage functionality. Examples of such circuitry may include, but are not limited or restricted to a hardware processor (e.g., microprocessor, one or more processor cores, a digital signal processor, a programmable gate array, a microcontroller, an application specific integrated circuit “ASIC”, etc.), a semiconductor memory, or combinatorial elements.

Additionally, or in the alternative, the term logic may refer to or include software such as one or more processes, one or more instances, Application Programming Interface(s) (API), subroutine(s), function(s), applet(s), servlet(s), routine(s), source code, object code, shared library/dynamic link library (dll), or even one or more instructions. This software may be stored in any type of a suitable non-transitory storage medium, or transitory storage medium (e.g., electrical, optical, acoustical or other form of propagated signals such as carrier waves, infrared signals, or digital signals). Examples of a non-transitory storage medium may include, but are not limited or restricted to a programmable circuit; non-persistent storage such as volatile memory (e.g., any type of random access memory “RAM”); or persistent storage such as non-volatile memory (e.g., read-only memory “ROM”, power-backed RAM, flash memory, phase-change memory, etc.), a solid-state drive, hard disk drive, an optical disc drive, or a portable memory device. As firmware, the logic may be stored in persistent storage.

Referring to FIG. 1A, an illustrative embodiment of a medical instrument monitoring system including a medical instrument with optic shape sensing and fiber optic-based oximetry capabilities is shown in accordance with some embodiments. As shown, the system 100 generally includes a console 110 and a stylet assembly 119 communicatively coupled to the console 110. For this embodiment, the stylet assembly 119 includes an elongate probe (e.g., stylet) 120 on its distal end 122 and a console connector 133 on its proximal end 124, where the stylet 120 is configured to advance within a patient vasculature either through, or in conjunction with, a catheter 195. The console connector 133 enables the stylet assembly 119 to be operably connected to the console 110 via an interconnect 145 including one or more optical fibers 147 (hereinafter, “optical fiber(s)”) and a conductive medium terminated by a single optical/electric connector 146 (or terminated by dual connectors. Herein, the connector 146 is configured to engage (mate) with the console connector 133 to allow for the propagation of light between the console 110 and the stylet assembly 119 as well as the propagation of electrical signals from the stylet 120 to the console 110.

An exemplary implementation of the console 110 includes a processor 160, a memory 165, a display 170 and optical logic 180, although it is appreciated that the console 110 can take one of a variety of forms and may include additional components (e.g., power supplies, ports, interfaces, etc.) that are not directed to aspects of the disclosure. An illustrative example of the console 110 is illustrated in U.S. Publication No. 2019/0237902, the entire contents of which are incorporated by reference herein. The processor 160, with access to the memory 165 (e.g., non-volatile memory or non-transitory, computer-readable medium), is included to control functionality of the console 110 during operation. As shown, the display 170 may be a liquid crystal diode (LCD) display integrated into the console 110 and employed as a user interface to display information to the clinician, especially during a catheter placement procedure (e.g., cardiac catheterization). In another embodiment, the display 170 may be separate from the console 110. Although not shown, a user interface is configured to provide user control of the console 110.

For both of these embodiments, the content depicted by the display 170 may change according to which mode the stylet 120 is configured to operate: optical, TLS, ECG, or another modality. In TLS mode, the content rendered by the display 170 may constitute a two-dimensional (2D) or three-dimensional (3D) representation of the physical state (e.g., length, shape, form, and/or orientation) of the stylet 120 computed from characteristics of reflected light signals 150 returned to the console 110. The reflected light signals 150 constitute light of a specific spectral width of broadband incident light 155 reflected back to the console 110. According to one embodiment of the disclosure, the reflected light signals 150 may pertain to various discrete portions (e.g., specific spectral widths) of broadband incident light 155 transmitted from and sourced by the optical logic 180, as described below

According to one embodiment of the disclosure, an activation control 126, included on the stylet assembly 119, may be used to set the stylet 120 into a desired operating mode and selectively alter operability of the display 170 by the clinician to assist in medical device placement. For example, based on the modality of the stylet 120, the display 170 of the console 110 can be employed for optical modality-based guidance during catheter advancement through the vasculature or TLS modality to determine the physical state (e.g., length, form, shape, orientation, etc.) of the stylet 120. In one embodiment, information from multiple modes, such as optical, TLS or ECG for example, may be displayed concurrently (e.g., at least partially overlapping in time).

Referring still to FIG. 1A, the optical logic 180 is configured to support operability of the stylet assembly 119 and enable the return of information to the console 110, which may be used to determine the physical state associated with the stylet 120 along with monitored electrical signals such as ECG signaling via an electrical signaling logic 181 that supports receipt and processing of the received electrical signals from the stylet 120 (e.g., ports, analog-to-digital conversion logic, etc.). The physical state of the stylet 120 may be based on changes in characteristics of the reflected light signals 150 received at the console 110 from the stylet 120. The characteristics may include shifts in wavelength caused by strain on certain regions of the core fibers integrated within an optical fiber core 135 positioned within or operating as the stylet 120, as shown below. As discussed herein, the optical fiber core 135 may be comprised of core fibers 137 ₁-137 _(M) (M=1 for a single core, and M≥2 for a multi-core), where the core fibers 137 ₁-137 _(M) may collectively be referred to as core fiber(s) 137. Unless otherwise specified or the instant embodiment requires an alternative interpretation, embodiments discussed herein will refer to a multi-core optical fiber 135. From information associated with the reflected light signals 150, the console 110 may determine (through computation or extrapolation of the wavelength shifts) the physical state of the stylet 120, and also that of the catheter 195 configured to receive the stylet 120.

According to one embodiment of the disclosure, as shown in FIG. 1A, the optical logic 180 may include a light source 182 and an optical receiver 184. The light source 182 is configured to transmit the incident light 155 (e.g., broadband) for propagation over the optical fiber(s) 147 included in the interconnect 145, which are optically connected to the multi-core optical fiber core 135 within the stylet 120. In one embodiment, the light source 182 is a tunable swept laser, although other suitable light sources can also be employed in addition to a laser, including semi-coherent light sources, LED light sources, etc.

The optical receiver 184 is configured to: (i) receive returned optical signals, namely reflected light signals 150 received from optical fiber-based reflective gratings (sensors) fabricated within each core fiber of the multi-core optical fiber 135 deployed within the stylet 120, and (ii) translate the reflected light signals 150 into reflection data (from repository 192), namely data in the form of electrical signals representative of the reflected light signals including wavelength shifts caused by strain. The reflected light signals 150 associated with different spectral widths may include reflected light signals 151 provided from sensors positioned in the center core fiber (reference) of the multi-core optical fiber 135 and reflected light signals 152 provided from sensors positioned in the periphery core fibers of the multi-core optical fiber 135, as described below. Herein, the optical receiver 184 may be implemented as a photodetector, such as a positive-intrinsic-negative “PIN” photodiode, avalanche photodiode, or the like.

As shown, both the light source 182 and the optical receiver 184 are operably connected to the processor 160, which governs their operation. Also, the optical receiver 184 is operably coupled to provide the reflection data (from repository 192) to the memory 165 for storage and processing by reflection data classification logic 190. The reflection data classification logic 190 may be configured to: (i) identify which core fibers pertain to which of the received reflection data (from repository 192) and (ii) segregate the reflection data stored with a repository 192 provided from reflected light signals 150 pertaining to similar regions of the stylet 120 or spectral widths into analysis groups. The reflection data for each analysis group is made available to shape sensing logic 194 for analytics.

According to one embodiment of the disclosure, the shape sensing logic 194 is configured to compare wavelength shifts measured by sensors deployed in each periphery core fiber at the same measurement region of the stylet 120 (or same spectral width) to the wavelength shift at a center core fiber of the multi-core optical fiber 135 positioned along central axis and operating as a neutral axis of bending. From these analytics, the shape sensing logic 194 may determine the shape the core fibers have taken in 3D space and may further determine the current physical state of the catheter 195 in 3D space for rendering on the display 170.

According to one embodiment of the disclosure, the shape sensing logic 194 may generate a rendering of the current physical state of the stylet 120 (and potentially the catheter 195), based on heuristics or run-time analytics. For example, the shape sensing logic 194 may be configured in accordance with machine-learning techniques to access a data store (library) with pre-stored data (e.g., images, etc.) pertaining to different regions of the stylet 120 (or catheter 195) in which reflected light from core fibers have previously experienced similar or identical wavelength shifts. From the pre-stored data, the current physical state of the stylet 120 (or catheter 195) may be rendered. Alternatively, as another example, the shape sensing logic 194 may be configured to determine, during run-time, changes in the physical state of each region of the multi-core optical fiber 135 based on at least: (i) resultant wavelength shifts experienced by different core fibers within the optical fiber 135, and (ii) the relationship of these wavelength shifts generated by sensors positioned along different periphery core fibers at the same cross-sectional region of the multi-core optical fiber 135 to the wavelength shift generated by a sensor of the center core fiber at the same cross-sectional region. It is contemplated that other processes and procedures may be performed to utilize the wavelength shifts as measured by sensors along each of the core fibers within the multi-core optical fiber 135 to render appropriate changes in the physical state of the stylet 120 (and/or catheter 195), especially to enable guidance of the stylet 120, when positioned at a distal tip of the catheter 195, within the vasculature of the patient and at a desired destination within the body.

The console 110 may further include electrical signaling logic 181, which is positioned to receive one or more electrical signals from the stylet 120. The stylet 120 is configured to support both optical connectivity as well as electrical connectivity. The electrical signaling logic 181 receives the electrical signals (e.g., ECG signals) from the stylet 120 via the conductive medium. The electrical signals may be processed by electrical signal logic 196, executed by the processor 160, to determine ECG waveforms for display.

Additionally, the console 110 includes a fluctuation logic 198 that is configured to analyze at least a subset of the wavelength shifts measured by sensors deployed in each of the core fibers 137. In particular, the fluctuation logic 198 is configured to analyze wavelength shifts measured by sensors of core fibers 137, where such corresponds to an analysis of the fluctuation of the distal tip of the stylet 120 (or “tip fluctuation analysis”). In some embodiments, the fluctuation logic 198 measures analyzes the wavelength shifts measured by sensors at a distal end of the core fibers 137. The tip fluctuation analysis includes at least a correlation of detected movements of the distal tip of the stylet 120 (or other medical device or instrument) with experiential knowledge comprising previously detected movements (fluctuations), and optionally, other current measurements such as ECG signals. The experiential knowledge may include previously detected movements in various locations within the vasculature (e.g., SVC, Inferior Vena Cava (IVC), right atrium, azygos vein, other blood vessels such as arteries and veins) under normal, healthy conditions and in the presence of defects (e.g., vessel constriction, vasospasm, vessel occlusion, etc.). Thus, the tip fluctuation analysis may result in a confirmation of tip location and/or detection of a defect affecting a blood vessel.

It should be noted that the fluctuation logic 198 need not perform the same analyses as the shape sensing logic 194. For instance, the shape sensing logic 194 determines a 3D shape of the stylet 120 by comparing wavelength shifts in outer core fibers of a multi-core optical fiber to a center, reference core fiber. The fluctuation logic 198 may instead correlate the wavelength shifts to previously measured wavelength shifts and optionally other current measurements without distinguishing between wavelength shifts of outer core fibers and a center, reference core fiber as the tip fluctuation analysis need not consider direction or shape within a 3D space.

In some embodiments, e.g., those directed at tip location confirmation, the analysis of the fluctuation logic 198 may utilize electrical signals (e.g., ECG signals) measured by the electrical signaling logic 181. For example, the fluctuation logic 198 may compare the movements of a subsection of the stylet 120 (e.g., the distal tip) with electrical signals indicating impulses of the heart (e.g., the heartbeat). Such a comparison may reveal whether the distal tip is within the SVC or the right atrium based on how closely the movements correspond to a rhythmic heartbeat.

In various embodiments, a display and/or alert may be generated based on the fluctuation analysis. For instance, the fluctuation logic 198 may generate a graphic illustrating the detected fluctuation compared to previously detected tip fluctuations and/or the anatomical movements of the patient body such as rhythmic pulses of the heart and/or expanding and contracting of the lungs. In one embodiment, such a graphic may include a dynamic visualization of the present medical device moving in accordance with the detected fluctuations adjacent to a secondary medical device moving in accordance with previously detected tip fluctuations. In some embodiments, the location of a subsection of the medical device may be obtained from the shape sensing logic 194 and the dynamic visualization may be location-specific (e.g., such that the previously detected fluctuations illustrate expected fluctuations for the current location of the subsection). In alternative embodiments, the dynamic visualization may illustrate a comparison of the dynamic movements of the subsection to one or more subsections moving in accordance with previously detected fluctuations of one or more defects affecting the blood vessel.

According to one embodiment of the disclosure, the fluctuation logic 198 may determine whether movements of one or more subsections of the stylet 120 indicate a location of a particular subsection of the stylet 120 or a defect affecting a blood vessel and, as a result, of the catheter 195, based on heuristics or run-time analytics. For example, the fluctuation logic 198 may be configured in accordance with machine-learning techniques to access a data store (library) with pre-stored data (e.g., experiential knowledge of previously detected tip fluctuation data, etc.) pertaining to different regions (subsections) of the stylet 120. Specifically, such an embodiment may include processing of a machine-learning model trained using the experiential knowledge, where the detected fluctuations serve as input to the trained model and processing of the trained model results in a determination as to how closely the detected fluctuations correlate to one or more locations within the vasculature of the patient and/or one or more defects affecting a blood vessel.

In some embodiments, the fluctuation logic 198 may be configured to determine, during run-time, whether movements of one or more subsections of the stylet 120 (and the catheter 195) indicate a location of a particular subsection of the stylet 120 or a defect affecting a blood vessel, based on at least (i) resultant wavelength shifts experienced by the core fibers 137 within the one or more subsections, and (ii) the correlation of these wavelength shifts generated by sensors positioned along different core fibers at the same cross-sectional region of the stylet 120 (or the catheter 195) to previously detected wavelength shifts generated by corresponding sensors in a core fiber at the same cross-sectional region. It is contemplated that other processes and procedures may be performed to utilize the wavelength shifts as measured by sensors along each of the core fibers 137 to render appropriate movements in the distal tip of the stylet 120 and/or the catheter 195.

Referring to FIG. 1B, an alternative exemplary embodiment of a medical instrument monitoring system 100 is shown. Herein, the medical instrument monitoring system 100 features a console 110 and a medical instrument 130 communicatively coupled to the console 110. For this embodiment, the medical instrument 130 corresponds to a catheter, which features an integrated tubing with two or more lumen extending between a proximal end 131 and a distal end 132 of the integrated tubing. The integrated tubing (sometimes referred to as “catheter tubing”) is in communication with one or more extension legs 140 via a bifurcation hub 142. An optical-based catheter connector 144 may be included on a proximal end of at least one of the extension legs 140 to enable the catheter 130 to operably connect to the console 110 via an interconnect 145 or another suitable component. Herein, the interconnect 145 may include a connector 146 that, when coupled to the optical-based catheter connector 144, establishes optical connectivity between one or more optical fibers 147 (hereinafter, “optical fiber(s)”) included as part of the interconnect 145 and core fibers 137 deployed within the catheter 130 and integrated into the tubing. Alternatively, a different combination of connectors, including one or more adapters, may be used to optically connect the optical fiber(s) 147 to the core fibers 137 within the catheter 130. The core fibers 137 deployed within the catheter 130 as illustrated in FIG. 1B include the same characteristics and perform the same functionalities as the core fibers 137 deployed within the stylet 120 of FIG. 1A.

The optical logic 180 is configured to support graphical rendering of the catheter 130, most notably the integrated tubing of the catheter 130, based on characteristics of the reflected light signals 150 received from the catheter 130. The characteristics may include shifts in wavelength caused by strain on certain regions of the core fibers 137 integrated within (or along) a wall of the integrated tubing, which may be used to determine (through computation or extrapolation of the wavelength shifts) the physical state of the catheter 130, notably its integrated tubing or a portion of the integrated tubing such as a tip or distal end of the tubing to read fluctuations (real-time movement) of the tip (or distal end).

More specifically, the optical logic 180 includes a light source 182. The light source 182 is configured to transmit the broadband incident light 155 for propagation over the optical fiber(s) 147 included in the interconnect 145, which are optically connected to multiple core fibers 137 within the catheter tubing. Herein, the optical receiver 184 is configured to: (i) receive returned optical signals, namely reflected light signals 150 received from optical fiber-based reflective gratings (sensors) fabricated within each of the core fibers 137 deployed within the catheter 130, and (ii) translate the reflected light signals 150 into reflection data (from repository 192), namely data in the form of electrical signals representative of the reflected light signals including wavelength shifts caused by strain. The reflected light signals 150 associated with different spectral widths include reflected light signals 151 provided from sensors positioned in the center core fiber (reference) of the catheter 130 and reflected light signals 152 provided from sensors positioned in the outer core fibers of the catheter 130, as described below.

As noted above, the shape sensing logic 194 is configured to compare wavelength shifts measured by sensors deployed in each outer core fiber at the same measurement region of the catheter (or same spectral width) to the wavelength shift at the center core fiber positioned along central axis and operating as a neutral axis of bending. From these analytics, the shape sensing logic 190 may determine the shape the core fibers have taken in 3D space and may further determine the current physical state of the catheter 130 in 3D space for rendering on the display 170.

According to one embodiment of the disclosure, the shape sensing logic 194 may generate a rendering of the current physical state of the catheter 130, especially the integrated tubing, based on heuristics or run-time analytics. For example, the shape sensing logic 194 may be configured in accordance with machine-learning techniques to access a data store (library) with pre-stored data (e.g., images, etc.) pertaining to different regions of the catheter 130 in which the core fibers 137 experienced similar or identical wavelength shifts. From the pre-stored data, the current physical state of the catheter 130 may be rendered. Alternatively, as another example, the shape sensing logic 194 may be configured to determine, during run-time, changes in the physical state of each region of the catheter 130, notably the tubing, based on at least (i) resultant wavelength shifts experienced by the core fibers 137 and (ii) the relationship of these wavelength shifts generated by sensors positioned along different outer core fibers at the same cross-sectional region of the catheter 130 to the wavelength shift generated by a sensor of the center core fiber at the same cross-sectional region. It is contemplated that other processes and procedures may be performed to utilize the wavelength shifts as measured by sensors along each of the core fibers 137 to render appropriate changes in the physical state of the catheter 130.

Referring to FIG. 2 , an exemplary embodiment of a structure of a section of the multi-core optical fiber included within the stylet 120 of FIG. 1A is shown in accordance with some embodiments. The multi-core optical fiber section 200 of the multi-core optical fiber 135 depicts certain core fibers 137 ₁-137 _(M) (M≥2, M=4 as shown, see FIG. 3A) along with the spatial relationship between sensors (e.g., reflective gratings) 210 ₁₁-210 _(NM) (N≥2; M≥2) present within the core fibers 137 ₁-137 _(M), respectively. As noted above, the core fibers 137 ₁-137 _(M) may be collectively referred to as “the core fibers 137.”

As shown, the section 200 is subdivided into a plurality of cross-sectional regions 220 ₁-220 _(N), where each cross-sectional region 220 ₁-220 _(N) corresponds to reflective gratings 210 ₁₁-210 ₁₄ . . . 210 _(N1)-210 _(N4). Some or all of the cross-sectional regions 220 ₁ . . . 220 _(N) may be static (e.g., prescribed length) or may be dynamic (e.g., vary in size among the regions 220 ₁ . . . 220 _(N)). A first core fiber 137 ₁ is positioned substantially along a center (neutral) axis 230 while core fiber 137 ₂ may be oriented within the cladding of the multi-core optical fiber 135, from a cross-sectional, front-facing perspective, to be position on “top” the first core fiber 137 ₁. In this deployment, the core fibers 137 ₃ and 137 ₄ may be positioned “bottom left” and “bottom right” of the first core fiber 137 ₁. As examples, FIGS. 3A-4B provides illustrations of such.

Referencing the first core fiber 137 ₁ as an illustrative example, when the stylet 120 is operative, each of the reflective gratings 210 ₁-210 _(N) reflects light for a different spectral width. As shown, each of the gratings 210 _(1i)-210 _(Ni) (1≤i≤M) is associated with a different, specific spectral width, which would be represented by different center frequencies of f₁ . . . f_(N), where neighboring spectral widths reflected by neighboring gratings are non-overlapping according to one embodiment of the disclosure.

Herein, positioned in different core fibers 137 ₂-137 ₃ but along at the same cross-sectional regions 220-220 _(N) of the multi-core optical fiber 135, the gratings 210 ₁₂-210 _(N2) and 210 ₁₃-210 _(N3) are configured to reflect incoming light at same (or substantially similar) center frequency. As a result, the reflected light returns information that allows for a determination of the physical state of the optical fibers 137 (and the stylet 120) based on wavelength shifts measured from the returned, reflected light. In particular, strain (e.g., compression or tension) applied to the multi-core optical fiber 135 (e.g., at least core fibers 137 ₂-137 ₃) results in wavelength shifts associated with the returned, reflected light. Based on different locations, the core fibers 137 ₁-137 ₄ experience different types and degree of strain based on angular path changes as the stylet 120 advances in the patient.

For example, with respect to the multi-core optical fiber section 200 of FIG. 2 , in response to angular (e.g., radial) movement of the stylet 120 is in the left-veering direction, the fourth core fiber 137 ₄ (see FIG. 3A) of the multi-core optical fiber 135 with the shortest radius during movement (e.g., core fiber closest to a direction of angular change) would exhibit compression (e.g., forces to shorten length). At the same time, the third core fiber 137 ₃ with the longest radius during movement (e.g., core fiber furthest from the direction of angular change) would exhibit tension (e.g., forces to increase length). As these forces are different and unequal, the reflected light from reflective gratings 210 _(N2) and 210 _(N3) associated with the core fibers 137 ₂ and 137 ₃ will exhibit different changes in wavelength. The differences in wavelength shift of the reflected light signals 150 can be used to extrapolate the physical configuration of the stylet 120 by determining the degrees of wavelength change caused by compression/tension for each of the periphery fibers (e.g., the second core fiber 137 ₂ and the third core fiber 137 ₃) in comparison to the wavelength of the reference core fiber (e.g., first core fiber 137 ₁) located along the neutral axis 230 of the multi-core optical fiber 135. These degrees of wavelength change may be used to extrapolate the physical state of the stylet 120. The reflected light signals 150 are reflected back to the console 110 via individual paths over a particular core fiber 137 ₁-137 _(M).

Referring to FIG. 3A, a first exemplary embodiment of the stylet of FIG. 1A supporting both an optical and electrical signaling is shown in accordance with some embodiments. Herein, the stylet 120 features a centrally located multi-core optical fiber 135, which includes a cladding 300 and a plurality of core fibers 137 ₁-137 _(M) (M≥2; M=4) residing within a corresponding plurality of lumens 320 ₁-320 _(M). While the multi-core optical fiber 135 is illustrated within four (4) core fibers 137 ₁-137 ₄, a greater number of core fibers 137 ₁-137 _(M) (M≥4) may be deployed to provide a more detailed three-dimensional sensing of the physical state (e.g., shape, etc.) of the multi-core optical fiber 135 and the stylet 120 deploying the optical fiber 135.

For this embodiment of the disclosure, the multi-core optical fiber 135 is encapsulated within a concentric braided tubing 310 positioned over a low coefficient of friction layer 335. The braided tubing 310 may feature a “mesh” construction, in which the spacing between the intersecting conductive elements is selected based on the degree of rigidity desired for the stylet 120, as a greater spacing may provide a lesser rigidity, and thereby, a more pliable stylet 120.

According to this embodiment of the disclosure, as shown in FIGS. 3A-3B, the core fibers 137 ₁-137 ₄ include (i) a central core fiber 137 ₁ and (ii) a plurality of periphery core fibers 137 ₂-137 ₄, which are maintained within lumens 320 ₁-320 ₄ formed in the cladding 300. According to one embodiment of the disclosure, one or more of the lumen 320 ₁-320 ₄ may be configured with a diameter sized to be greater than the diameter of the core fibers 137 ₁-137 ₄. By avoiding a majority of the surface area of the core fibers 137 ₁-137 ₄ from being in direct physical contact with a wall surface of the lumens 320 ₁-320 ₄, the wavelength changes to the incident light are caused by angular deviations in the multi-core optical fiber 135 thereby reducing influence of compression and tension forces being applied to the walls of the lumens 320 ₁-320 _(M), not the core fibers 137 ₁-137 _(M) themselves.

As further shown in FIGS. 3A-3B, the core fibers 137 ₁-137 ₄ may include central core fiber 137 ₁ residing within a first lumen 320 ₁ formed along the first neutral axis 230 and a plurality of core fibers 137 ₂-137 ₄ residing within lumens 320 ₂-320 ₄ each formed within different areas of the cladding 300 radiating from the first neutral axis 230. In general, the core fibers 137 ₂-137 ₄, exclusive of the central core fiber 137 ₁, may be positioned at different areas within a cross-sectional area 305 of the cladding 300 to provide sufficient separation to enable three-dimensional sensing of the multi-core optical fiber 135 based on changes in wavelength of incident light propagating through the core fibers 137 ₂-137 ₄ and reflected back to the console for analysis.

For example, where the cladding 300 features a circular cross-sectional area 305 as shown in FIG. 3B, the core fibers 137 ₂-137 ₄ may be positioned substantially equidistant from each other as measured along a perimeter of the cladding 300, such as at “top” (12 o'clock), “bottom-left” (8 o'clock) and “bottom-right” (4 o'clock) locations as shown. Hence, in general terms, the core fibers 137 ₂-137 ₄ may be positioned within different segments of the cross-sectional area 305. Where the cross-sectional area 305 of the cladding 300 has a distal tip 330 and features a polygon cross-sectional shape (e.g., triangular, square, rectangular, pentagon, hexagon, octagon, etc.), the central core fiber 137 ₁ may be located at or near a center of the polygon shape, while the remaining core fibers 137 ₂-137 _(M) may be located proximate to angles between intersecting sides of the polygon shape.

Referring still to FIGS. 3A-3B, operating as the conductive medium for the stylet 120, the braided tubing 310 provides mechanical integrity to the multi-core optical fiber 135 and operates as a conductive pathway for electrical signals. For example, the braided tubing 310 may be exposed to a distal tip of the stylet 120. The cladding 300 and the braided tubing 310, which is positioned concentrically surrounding a circumference of the cladding 300, are contained within the same insulating layer 350. The insulating layer 350 may be a sheath or conduit made of protective, insulating (e.g., non-conductive) material that encapsulates both for the cladding 300 and the braided tubing 310, as shown.

Referring to FIG. 4A, a second exemplary embodiment of the stylet of FIG. 1A is shown in accordance with some embodiments. Referring now to FIG. 4A, a second exemplary embodiment of the stylet 120 of FIG. 1A supporting both an optical and electrical signaling is shown. Herein, the stylet 120 features the multi-core optical fiber 135 described above and shown in FIG. 3A, which includes the cladding 300 and the first plurality of core fibers 137 ₁-137 _(M) (M≥3; M=4 for embodiment) residing within the corresponding plurality of lumens 320 ₁-320 _(M). For this embodiment of the disclosure, the multi-core optical fiber 135 includes the central core fiber 137 ₁ residing within the first lumen 320 ₁ formed along the first neutral axis 230 and the second plurality of core fibers 137 ₂-137 ₄ residing within corresponding lumens 320 ₂-320 ₄ positioned in different segments within the cross-sectional area 305 of the cladding 300. Herein, the multi-core optical fiber 135 is encapsulated within a conductive tubing 400. The conductive tubing 400 may feature a “hollow” conductive cylindrical member concentrically encapsulating the multi-core optical fiber 135.

Referring to FIGS. 4A-4B, operating as a conductive medium for the stylet 120 in the transfer of electrical signals (e.g., ECG signals) to the console, the conductive tubing 400 may be exposed up to a tip 410 of the stylet 120. For this embodiment of the disclosure, a conductive epoxy 420 (e.g., metal-based epoxy such as a silver epoxy) may be affixed to the tip 410 and similarly joined with a termination/connection point created at a proximal end 430 of the stylet 120. The cladding 300 and the conductive tubing 400, which is positioned concentrically surrounding a circumference of the cladding 300, are contained within the same insulating layer 440. The insulating layer 440 may be a protective conduit encapsulating both for the cladding 300 and the conductive tubing 400, as shown.

Referring to FIG. 5A, an elevation view of a first illustrative embodiment of a catheter including integrated tubing, a diametrically disposed septum, and micro-lumens formed within the tubing and septum is shown in accordance with some embodiments. Herein, the catheter 130 includes integrated tubing, the diametrically disposed septum 510, and the plurality of micro-lumens 530 ₁-530 ₄ which, for this embodiment, are fabricated to reside within the wall 500 of the integrated tubing of the catheter 130 and within the septum 510. In particular, the septum 510 separates a single lumen, formed by the inner surface 505 of the wall 500 of the catheter 130, into multiple lumen, namely two lumens 540 and 545 as shown. Herein, the first lumen 540 is formed between a first arc-shaped portion 535 of the inner surface 505 of the wall 500 forming the catheter 130 and a first outer surface 555 of the septum 510 extending longitudinally within the catheter 130. The second lumen 545 is formed between a second arc-shaped portion 565 of the inner surface 505 of the wall 500 forming the catheter 130 and a second outer surfaces 560 of the septum 510.

According to one embodiment of the disclosure, the two lumens 540 and 545 have approximately the same volume. However, the septum 510 need not separate the tubing into two equal lumens. For example, instead of the septum 510 extending vertically (12 o'clock to 6 o'clock) from a front-facing, cross-sectional perspective of the tubing, the septum 510 could extend horizontally (3 o'clock to 9 o'clock), diagonally (1 o'clock to 7 o'clock; 10 o'clock to 4 o'clock) or angularly (2 o'clock to 10 o'clock). In the later configuration, each of the lumens 540 and 545 of the catheter 130 would have a different volume.

With respect to the plurality of micro-lumens 530 ₁-530 ₄, the first micro-lumen 530 ₁ is fabricated within the septum 510 at or near the cross-sectional center 525 of the integrated tubing. For this embodiment, three micro-lumens 530 ₂-530 ₄ are fabricated to reside within the wall 500 of the catheter 130. In particular, a second micro-lumen 530 ₂ is fabricated within the wall 500 of the catheter 130, namely between the inner surface 505 and outer surface 507 of the first arc-shaped portion 535 of the wall 500. Similarly, the third micro-lumen 530 ₃ is also fabricated within the wall 500 of the catheter 130, namely between the inner and outer surfaces 505/507 of the second arc-shaped portion 555 of the wall 500. The fourth micro-lumen 530 ₄ is also fabricated within the inner and outer surfaces 505/507 of the wall 500 that are aligned with the septum 510.

According to one embodiment of the disclosure, as shown in FIG. 5A, the micro-lumens 530 ₂-530 ₄ are positioned in accordance with a “top-left” (10 o'clock), “top-right” (2 o'clock) and “bottom” (6 o'clock) layout from a front-facing, cross-sectional perspective. Of course, the micro-lumens 530 ₂-530 ₄ may be positioned differently, provided that the micro-lumens 530 ₂-530 ₄ are spatially separated along the circumference 520 of the catheter 130 to ensure a more robust collection of reflected light signals from the outer core fibers 570 ₂-570 ₄ when installed. For example, two or more of micro-lumens (e.g., micro-lumens 530 ₂ and 530 ₄) may be positioned at different quadrants along the circumference 520 of the catheter wall 500.

Referring to FIG. 5B, a perspective view of the first illustrative embodiment of the catheter of FIG. 5A including core fibers installed within the micro-lumens is shown in accordance with some embodiments. According to one embodiment of the disclosure, the second plurality of micro-lumens 530 ₂-530 ₄ are sized to retain corresponding outer core fibers 570 ₂-570 ₄, where the diameter of each of the second plurality of micro-lumens 530 ₂-530 ₄ may be sized just larger than the diameters of the outer core fibers 570 ₂-570 ₄. The size differences between a diameter of a single core fiber and a diameter of any of the micro-lumen 530 ₁-530 ₄ may range between 0.001 micrometers (μm) and 1000 μm, for example. As a result, the cross-sectional areas of the outer core fibers 570 ₂-570 ₄ would be less than the cross-sectional areas of the corresponding micro-lumens 530 ₂-530 ₄. A “larger” micro-lumen (e.g., micro-lumen 530 ₂) may better isolate external strain being applied to the outer core fiber 570 ₂ from strain directly applied to the catheter 130 itself. Similarly, the first micro-lumen 530 ₁ may be sized to retain the center core fiber 570 ₁, where the diameter of the first micro-lumen 530 ₁ may be sized just larger than the diameter of the center core fiber 570 ₁.

As an alternative embodiment of the disclosure, one or more of the micro-lumens 530 ₁-530 ₄ may be sized with a diameter that exceeds the diameter of the corresponding one or more core fibers 570 ₁-570 ₄. However, at least one of the micro-lumens 530 ₁-530 ₄ is sized to fixedly retain their corresponding core fiber (e.g., core fiber retained with no spacing between its lateral surface and the interior wall surface of its corresponding micro-lumen). As yet another alternative embodiment of the disclosure, all the micro-lumens 530 ₁-530 ₄ are sized with a diameter to fixedly retain the core fibers 570 ₁-570 ₄.

Referring to FIGS. 6A-6B, flowcharts of methods of operations conducted by the medical instrument monitoring system of FIGS. 1A-1B to achieve optic 3D shape sensing are shown in accordance with some embodiments. Herein, the catheter includes at least one septum spanning across a diameter of the tubing wall and continuing longitudinally to subdivide the tubing wall. The medial portion of the septum is fabricated with a first micro-lumen, where the first micro-lumen is coaxial with the central axis of the catheter tubing. The first micro-lumen is configured to retain a center core fiber. Two or more micro-lumen, other than the first micro-lumen, are positioned at different locations circumferentially spaced along the wall of the catheter tubing. For example, two or more of the second plurality of micro-lumens may be positioned at different quadrants along the circumference of the catheter wall.

Furthermore, each core fiber includes a plurality of sensors spatially distributed along its length between at least the proximal and distal ends of the catheter tubing. This array of sensors is distributed to position sensors at different regions of the core fiber to enable distributed measurements of strain throughout the entire length or a selected portion of the catheter tubing. These distributed measurements may be conveyed through reflected light of different spectral widths (e.g., specific wavelength or specific wavelength ranges) that undergoes certain wavelength shifts based on the type and degree of strain.

According to one embodiment of the disclosure, as shown in FIG. 6A, for each core fiber, broadband incident light is supplied to propagate through a particular core fiber (block 600). Unless discharged, upon the incident light reaching a sensor of a distributed array of sensors measuring strain on a particular core fiber, light of a prescribed spectral width associated with the first sensor is to be reflected back to an optical receiver within a console (blocks 605-610). Herein, the sensor alters characteristics of the reflected light signal to identify the type and degree of strain on the particular core fiber as measured by the first sensor (blocks 615-620). According to one embodiment of the disclosure, the alteration in characteristics of the reflected light signal may signify a change (shift) in the wavelength of the reflected light signal from the wavelength of the incident light signal associated with the prescribed spectral width. The sensor returns the reflected light signal over the core fiber and the remaining spectrum of the incident light continues propagation through the core fiber toward a distal end of the catheter tubing (blocks 625-630). The remaining spectrum of the incident light may encounter other sensors of the distributed array of sensors, where each of these sensors would operate as set forth in blocks 605-630 until the last sensor of the distributed array of sensors returns the reflected light signal associated with its assigned spectral width and the remaining spectrum is discharged as illumination.

Referring now to FIG. 6B, during operation, multiple reflected light signals are returned to the console from each of the plurality of core fibers residing within the corresponding plurality of micro-lumens formed within a catheter, such as the catheter of FIG. 1B. In particular, the optical receiver receives reflected light signals from the distributed arrays of sensors located on the center core fiber and the outer core fibers and translates the reflected light signals into reflection data, namely electrical signals representative of the reflected light signals including wavelength shifts caused by strain (blocks 650-655). The reflection data classification logic is configured to identify which core fibers pertain to which reflection data and segregate reflection data provided from reflected light signals pertaining to a particular measurement region (or similar spectral width) into analysis groups (block 660-665).

Each analysis group of reflection data is provided to shape sensing logic for analytics (block 670). Herein, the shape sensing logic compares wavelength shifts at each outer core fiber with the wavelength shift at the center core fiber positioned along central axis and operating as a neutral axis of bending (block 675). From this analytics, on all analytic groups (e.g., reflected light signals from sensors in all or most of the core fibers), the shape sensing logic may determine the shape the core fibers have taken in three-dimensional space, from which the shape sensing logic can determine the current physical state of the catheter in three-dimension space (blocks 680-685).

Referring to FIG. 7 , an exemplary embodiment of the medical instrument monitoring system of FIG. A1 during operation and insertion of the catheter into a patient are shown in accordance with some embodiments. Herein, the catheter 195 generally includes integrated tubing with a proximal portion 720 that generally remains exterior to the patient 700 and a distal portion 730 that generally resides within the patient vasculature after placement is complete, where the catheter 195 enters the vasculature at insertion site 710. The stylet 120 may be advanced through the catheter 195 to a desired position within the patient vasculature such that a distal end (or tip) 735 of the stylet 120 (and hence a distal end of the catheter 195) is proximate the patient's heart, such as in the lower one-third (⅓) portion of the Superior Vena Cava (“SVC”) for example. For this embodiment, various instruments may be placed at the distal end 735 of the stylet 120 and/or the catheter 195 to measure pressure of blood in a certain heart chamber and in the blood vessels, view an interior of blood vessels, or the like.

During advancement through a patient vasculature, the stylet 120 receives broadband incident light 155 from the console 110 via optical fiber(s) 147 within the interconnect 145, where the incident light 155 propagates to the core fibers 137 within the stylet 120. According to one embodiment of the disclosure, the connector 146 of the interconnect 145 terminating the optical fiber(s) 147 may be coupled to the optical-based catheter connector 144, which may be configured to terminate the core fibers 137 deployed within the stylet 120. Such coupling optically connects the core fibers 137 of the stylet 120 with the optical fiber(s) 147 within the interconnect 145. The optical connectivity is needed to propagate the incident light 155 to the core fibers 137 and return the reflected light signals 150 to the optical logic 180 within the console 110 over the interconnect 145 The physical state of the stylet 120 may be ascertained based on analytics of the wavelength shifts of the reflected light signals 150.

Referring now to FIG. 8 , an embodiment of a structure of a section of a single core optical fiber included within a stylet 800 that is kinked or damaged is shown in accordance with some embodiments. The single core optical fiber section 801 of the optical fiber 836 depicts a singular core fiber 837 along with the spatial relationship between sensors (e.g., reflective gratings) 810 ₁-810 _(N) (N≥2) present within the core fiber. As shown, the single core optical fiber 836 included within a stylet 800 is similar to the multi-core optical fiber section 200 of FIG. 2 , such that the discussion about regarding the functionality of the sensors (reflective gratings) 210 ₁₁-210 _(NM) (N≥2; M≥2) present within the core fibers 137 ₁-137 _(M), respectively of FIG. 2 , applies to the reflective gratings 810 ₁-810 _(N) present within the core fiber 837. For instance, the single core optical fiber section 801 is subdivided into a plurality of cross-sectional regions 820 ₁-820 _(N), where each cross-sectional region 820 ₁-820 _(N) corresponds to a reflective grating 810 ₁-810 _(N). Some or all of the cross-sectional regions 820 ₁ . . . 820 _(N) may be static (e.g., prescribed length) or may be dynamic (e.g., vary in size among the regions 820 ₁ . . . 820 _(N)).

The core fiber 837 is positioned substantially along a center axis 830 within the cladding of the single core optical fiber 836. When stylet 800 is operative, each of the reflective gratings 810 ₁-810 _(N) reflects light for a different spectral width. As shown, each of the gratings 810 ₁-810 _(N) is associated with a different, specific spectral width, which would be represented by different center frequencies of f₁ . . . f_(N), where neighboring spectral widths reflected by neighboring gratings are non-overlapping according to one embodiment of the disclosure.

As a result, the reflected light returns information that allows for a determination of the physical state of the single core optical fiber 836 (and the stylet 800) based on wavelength shifts measured from the returned, reflected light. In particular, strain (e.g., compression or tension) applied to the single core optical fiber 836 results in wavelength shifts associated with the returned, reflected light. Based on different locations, the core fiber 837 experiences different types and degree of strain based on angular path changes as the stylet 800 advances in the patient.

In a healthy, operative state, the reflective gratings 810 ₁-810 _(N) receive broadband incident land 155 and reflect light having different spectral widths such that logic of the console 110 may determine a physical state of the single core optical fiber 836 (and the stylet 800). However, when damage occurs to the single core optical fiber 836 or a kink develops, the receipt of the incident light 155 by each of the reflective gratings 810 ₁-810 _(N) and the corresponding reflection of light signals may be impaired, preventing the logic of the console 110 from determining the physical state of the single core optical fiber 836 (and the stylet 800). In some instances, the incident light 155 is unable to propagate beyond the damage.

In particular, FIG. 8 illustrates the single core optical fiber 836 following an occurrence of damage resulting in damage 840. Examples of damage may include, but are not limited or restricted to, cracking of the core fiber (excess tension, e.g., during cable pulling or despoiling) or bending of the core fiber on too tight of a radius (excess tension or excess compression). In some instances, excessively bending a core fiber (i.e., bending beyond the core fiber bend radius) may also cause micro-cracks in the core fiber resulting in permanent damage, which may result in a reflected wavelength peak overlap degrading the ability for the logic to determine the shape of the core fiber.

As shown, the damage 840 is present within the cross-sectional region 820 ₂ at a location that is proximal the reflective gratings 810 ₂-810 _(N). The damage 840 may alter the incident light 155 that propagates beyond the damage 840 (resulting in propagation of the altered incident light 156) or prevent light from passing to a location distal the damage 840 (i.e., due to a complete break or fracture).

As a result, the console 110 may receive reflected light signals 842 ₁-842 _(N), where one or more of the reflected light signals 842 ₂-842 _(N) are have unexpected spectral widths due to the altered incident light 156, and/or may not receive reflected light signals from one or more of the reflective gratings 810 ₂-810 _(N) due to the inability of a reflective grating to reflect the altered incident light 156. In embodiments in which incident light is prevented from propagating beyond the damage 840, reflected light signals will only be received from reflective gratings that are proximal the damage 840 (e.g., the reflective grating 810 ₁). As a result of the damage 840, the logic of the console 110 is unable to determine a physical state of the single core optical fiber 836 (or the stylet 800) for at least the portion of the single core optical fiber 836 comprised of the cross-sectional regions 820 ₂-820 _(N).

When the console 110 receives the reflected light signal 842 ₁ and, in instances when the altered incident light 156 propagates beyond the damage 840, one or more of reflected light signals 842 ₂-842 _(N), the optical receiver 184 processes the received reflected light signals and provides such to the reflection data classification logic 190, which further processes the received reflected light signals as discussed above. The core fiber health detection logic 191 may then analyze received reflected light signals for unexpected spectral widths (each reflective grating is configured to reflect incident light at a specific spectral width) or for a lack of receipt of one or more expected spectral widths. Thus, when one or more of the reflected light signals 842 ₂-842 _(N) are received, each includes unexpected spectral widths (i.e., not matching those assigned to each of the reflective gratings 810 ₂-810 _(N)), the core fiber health detection logic 191 determines that damage has occurred to the core fiber 837.

Further, in some embodiments, the specific spectral width of each received reflected light signal may be analyzed to determine a location along the core fiber 837 at which damage (or a kink) occurred. Specifically, the core fiber health detection logic 191 may further analyze each of the received light signals to identify (i) a most distal reflective grating from which a normal, uncorrupted light signal was received, and a (ii) a most proximal reflective grating from which a corrupted (e.g., degraded) light signal was received. Such an identification of reflective gratings results in an identification of the location of the kink or point of damage. Thus, by determining that the most distal reflective grating from which a reflected light signal having an expected spectral width was received is the reflective grating 810 ₁ and the most proximal reflective grating from which a reflected light signal having an unexpected spectral width was received is the reflective grating 810 ₂, the core fiber health detection logic 191 identifies the location of the damage 840 (i.e., between the reflective gratings 810 ₁ and 810 ₂). In embodiments in which the incident light 155 is prevented from propagating beyond the damage 840, the location of the damage 840 is determined to be based on the lack of reflected light signals received from any of 810 ₂-810 _(N).

In some embodiments, the core fiber health detection logic 191 may be configured to generate an alert indicating that the optical fiber 836 has been damaged, and, optionally, identifying the location of the damage. The alert may be provided or rendered by the console 110, or transmitted to an alternative electronic device (e.g., a speaker or display not integrated into the console 110, a network device such as a mobile device, etc.). For example, the alert may be an audio/visual indication that damage has occurred. In some embodiments, the alert may be generated by a separate logic module, such an as alert generation logic (not shown).

In some embodiments, the core fiber health detection logic 191 may also be configured to analyze each of the received light signals to identify particular strain detected by reflective gratings. The identified strain may be compared to previously identified strain that corresponds to positioning or a shape of the core fiber 137 that has a high likelihood of resulting in damage to the core fiber 137. The information pertaining to the previously identified strain may be stored as part of the reflection data 192. In some embodiments, the core fiber health detection logic 191 may operate in combination with the shape sensing logic 192 in identifying shapes of the core fiber 137 (e.g., the core fiber health detection logic 191 may compare a shape of the core fiber 137 against stored shapes known to have a high likelihood of causing damage to the core fiber 137). Thus, the core fiber health detection logic 191 may analyze received light signals to determine whether the current shape of the core fiber 137 (or stylet or catheter within which the core fiber 137 is disposed or otherwise affixed) is within a threshold percentage of matching a shape known to have a high likelihood of causing damage. More broadly, the core fiber health detection logic 191 may analyze received light signals to determine whether the strain currently being experienced by the core fiber 137 (or stylet or catheter within which the core fiber 137 is disposed or otherwise affixed) is within a threshold percentage of matching strain known to have a high likelihood of causing damage. When the shape or strain of the core fiber 137 is similar to a shape or strain known to have a high likelihood of causing damage, the core fiber health detection logic 191 may cause an alert to be generated. In some embodiments, being “similar to a shape or strain” may refer to the identified shape or strain being within a threshold percentage of matching a shape or strain known to have a high likelihood of causing damage

In embodiments, the core fiber health detection logic 191 may also extrapolate the reflection data of a core fiber 137 to predict a future shape (and corresponding strain) of the core fiber 137. When the extrapolated shape or strain of the core fiber 137 is similar to a shape or strain known to have a high likelihood of causing damage, the core fiber health detection logic 191 may cause an alert to be generated. In some embodiments, being “similar to a shape or strain” may refer to the extrapolated shape or strain being within a threshold percentage of matching a shape or strain known to have a high likelihood of causing damage. Further, the core fiber health detection logic 191 may perform a similar analysis on the received light signals to determine whether a stylet and/or catheter within which the core fiber is disposed (or otherwise affixed) is currently in a shape or be experiencing strain known to have a high likelihood of causing damage. Similarly, the core fiber health detection logic 191 may perform a similar analysis on the received light signals to determine whether a stylet and/or catheter within which the core fiber is disposed (or otherwise affixed) has prolapsed.

Referring to FIG. 9A, an embodiment of the structure of the section of the multi-core optical fiber of FIG. 2 included within the stylet 120 of FIG. 1A that is kinked or partially damaged is shown in accordance with some embodiments. As discussed previously, the multi-core optical fiber section 200 of the optical fiber core 136 depicts certain core fibers 137 ₁-137 ₄ along with the spatial relationship between sensors 210 ₁₁-210 _(NM) present within the core fibers 137 ₁-137 ₄, respectively. As shown, the section 200 is subdivided into a plurality of cross-sectional regions 220 ₁-220 _(N), where each cross-sectional region 220 ₁-220 _(N) corresponds to reflective gratings 210 ₁₁-210 ₁₄ . . . 210 _(N1)-210 _(N4).

However, differently than FIG. 2 , FIG. 9A illustrates the multi-core optical fiber section 200 including damage 900, where the damage 900 affects the core fiber 137 ₂ within the cross-sectional region 220 ₂ between the reflective grating 210 ₁₂ and the reflective grating 210 ₂₂. The damage 900 may a result of one or more various factors including kinking and/or excess strain (compression or tension) placed on the core fiber 137 ₂. Additionally, or in the alternatively, blunt physical force incurred by the core fiber 137 ₂ may result in the damage 900. Detection of the damage 900 is beneficial such that an alert may be generated notifying a user of such. For example, a physician improperly trimming a catheter without pulling back a stylet including an optical fiber would be immediately notified through generation of an alert that their practice is impacting system functionality.

As shown in the illustration, the incident light 155 propagates along the length of each of the core fibers 137 ₁-137 ₄ such that reflective gratings disposed thereon may reflect light signals back to the console 110. However, in some instances, the damage 900 may affect the incident light propagating along the length of the core fiber 137 ₂ such that altered incident light 156 propagated along the length of the core fiber 137 ₂ distal the point along the core fiber 137 ₂ at which the damage 900 occurred (“point of damage 900”). The altered incident 156 light may be degraded or altered in any manner, which may affect the ability of the reflective gratings 210 ₂₂-210 _(N2) from reflecting light signals in accordance with the applied strain on the corresponding cross-sectional region. In some embodiments, the incident light 155 is unable to propagate past the damage 900 altogether.

More specifically, the damage 900 causes an alteration in the incident light 155 propagating along the core fiber 137 ₂ resulting in the altered incident light 156 to propagate distal the damage 900, where the altered incident 156 may be a portion of incident light 155. The reflected light signal 902 is reflected by one or more of the reflective gratings distal the damage 900 (i.e., reflective gratings 210 ₂₂-210 _(N2)), wherein the reflected light signal 902 includes reflected light signals having unexpected spectral widths. In some instances, the reflected light signal 902 includes reflected light signals from less than all of the reflective gratings 210 ₂₂-210 _(N2)) (i.e., one or more of the reflective gratings 210 ₂₂-210 _(N2) did not reflect a light signal). In some embodiments, the damage 900 may be a complete breakage or fracture of the core fiber 137 ₂ such that no portion of the incident light 155 is able propagate past the damage 900. In such instances, the reflective gratings 210 ₂₂-210 _(N2) would not reflect the reflected light signal 902.

Upon receipt of the reflected light signals 152 ₁-152 ₄ and 902 by the console 110, the optical receiver 184 processes the received reflected light signals and provides such to the reflection data classification logic 190, which further processes the received reflected light signals as discussed above. The core fiber health detection logic 191 may then analyze received reflected light signals corresponding to each core fiber 137 ₁-137 ₄. In one embodiment, each core fiber 137 ₁-137 ₄ is assigned with a unique identifier (ID) to which each reflected light signal is associated. Thus, association of a reflected light signal with a specific core fiber 137 ₁-137 ₄ is maintained via the unique ID of each core fiber 137 ₁-137 ₄.

Specifically, detection of damage to a core fiber 137 ₁-137 ₁ is performed by analyzing the received reflected light signals 152 ₁-152 ₄ and 902 for unexpected spectral widths (each reflective grating is configured to reflect incident light at a specific spectral width) or for a lack of receipt of one or more expected spectral widths. Thus, as the reflected light signal 902 includes unexpected spectral widths (i.e., not matching those assigned to each of the reflective gratings 210 ₂₂-210 _(N2)), the core fiber health detection logic 191 determines that damage has occurred to the core fiber 137 ₂.

Further, in some embodiments, the specific spectral width of each received reflected light signal may be analyzed to determine a location along the core fiber 137 ₂ at which damage (or a kink) occurred. As the core fiber health detection logic 191 (or more generally, the reflection data classification logic 190) determined that the unexpected spectral width within the received light signal 902 was received from the core fiber 137 ₂, the core fiber health detection logic 191 may further analyze each of the received light signals 1522 and 902 to identify (i) a most distal reflective grating from which a normal, uncorrupted light signal was received, and a (ii) a most proximal reflective grating from which a corrupted (e.g., degraded) light signal was received. Such an identification of reflective gratings results in an identification of the location of the kink or point of damage. Thus, by determining that the most distal reflective grating from which a reflected light signal having an expected spectral width was received is the reflective grating 210 ₁₂ and the most proximal reflective grating from which a reflected light signal having an unexpected spectral width was received is the reflective grating 210 ₂₂, the core fiber health detection logic 191 identifies the location of the damage 900 (i.e., between the reflective gratings 210 ₁₂ and 210 ₂₂).

Although damage may degrade or otherwise alter the operability of one or more core fibers, optical fibers that include redundant core fibers may maintain complete or partial functionality beyond the point of damage. As illustrated in FIG. 9A, the core fiber 137 ₂ is shown to be damaged within the cross-sectional region 220 ₂ while the core fibers 137 ₁ and 137 ₃-137 ₄ have not incurred damaged; thus, some functionality of the multi-core optical fiber 136 may be maintained via reflected signals received from the core fibers 137 ₁ and 137 ₃-137 ₄.

For example, in some embodiments, a stylet may be configured to perform several measurements and/or take several readings during advancement through a catheter lumen, such that the measurements and readings are provided to logic of a console, such as the console 110, for processing. For example, a multi-core optical fiber may be integrated within the stylet along with one or more pulse oximetry sensors and/or one or more electrodes for intravascular electrocardiogram (ECG) monitoring. Such a stylet provides measurements and readings to the console 110 for analyses that determine a physical state (e.g., shape) of the stylet, whether the distal tip of the stylet has entered the Azygos vein, an amount of fluctuation of the distal tip of the stylet, a level of oxygen in the patient's blood, and location tracking of the distal tip of the stylet via ECG monitoring. In instances in which one or more core fibers of the multi-core optical fiber are damaged, the stylet is still operable obtain measurements and/or readings pertaining to one or more of the functionalities described above. For example, in the even that one or more core fibers are damaged, the stylet may still be functional to provide information pertaining to whether the distal tip of the stylet has entered the Azygos vein, an amount of fluctuation of the distal tip of the stylet, a level of oxygen in the patient's blood, and location tracking of the distal tip of the stylet via ECG monitoring.

One or more embodiments of the disclosure may include a body of implementation configured to perform any combination of the following functions: fiber optic fluctuation sensing/monitoring, fiber optic shape sensing, fiber optic oximetry monitoring, distal tip placement confirmation, distal tip location/tracking, Azygos vein detection, impedance/conductance sensing, intravascular ECG monitoring, and/or fiber optic vein/artery cannulation detection. As discussed above, such a body of implementation is configured to maintain the ability to perform one or more of these functionalities when one or more of the core fibers of the multi-core optical fiber integrated into the body of implementation are damaged or kinked such and non-functional past the kink or point of damage.

Additionally, the multi-core optical fiber 136 may include a number of core fibers greater than illustrated in the figures included herein, which may provide sufficient redundancy to maintain the shape sensing functionality past the point of damage. In order to maintain the ability to perform shape sensing past the point of damage, the number of operable core fibers (i.e., those capable of receiving incident light and reflecting light signals to the console 110 without such a degradation that prevents the shape sensing logic 194 from determining the physical state of the stylet/catheter with a level of confidence). As one exemplary embodiment, a multi-core optical fiber having seven or more core fibers would include sufficient redundancy to maintain shape sensing functionalities past a point of damage when one of the seven core fibers is non-functional past the point of damage.

In some embodiments, however, an optical fiber may not include sufficient redundancy in order to preserve shape sensing capabilities due to damage. For example, with reference to FIG. 9A that includes four periphery cores and one central core, damage at a periphery core would not maintain shape sensing capabilities. However, damage to only the central core with four properly functioning periphery cores would have redundant shape sensing capability.

Referring to FIG. 9B, an embodiment of a structure of a section of a multi-core optical fiber included within the stylet 120 of FIG. 1A that is completely damaged is shown in accordance with some embodiments. In the same manner as discussed above with respect to FIG. 9A, the core fiber health detection logic 191 analyzes reflected light signals 906 ₁-906 ₄ for unexpected spectral widths (or a lack of expected spectral widths).

Thus, as the reflected light signal 152 ₁-152 ₄ and 906 ₁-906 ₄ for include unexpected spectral widths (i.e., not matching those assigned to each of the reflective gratings 210 ₁₁-210 ₁₄ . . . 210 _(N1)-210 _(N4).), the core fiber health detection logic 191 determines that damage 904 has occurred affecting each of the core fibers 137 ₁-137 ₄.

As also discussed above with respect to FIG. 9A, the specific spectral width of each received reflected light signal may be analyzed to determine a location along the core fibers 137 ₁-137 ₄ at which the damage (or a kink) occurred. The core fiber health detection logic 191 may further analyze each of the reflected light signals 152 ₁-152 ₄ and 906 ₁-906 ₄ to identify (i) a most distal reflective grating from which a normal, uncorrupted light signal was received, and a (ii) a most proximal reflective grating from which a corrupted (e.g., degraded) light signal was received. Thus, by determining that the most distal reflective grating from which a reflected light signal having an expected spectral width was received is the reflective gratings 210 ₁₁, 210 ₁₂, 210 ₁₃ and 210 ₁₄ (referring to the core fibers 137 ₁-137 ₄, respectively) and the most proximal reflective grating from which a reflected light signal having an unexpected spectral width was received is the reflective gratings 210 ₂₁, 210 ₂₂, 210 ₂₃ and 210 ₂₄ (referring to the core fibers 137 ₁-137 ₄, respectively), the core fiber health detection logic 191 identifies the location of the damage 904.

Although damage may degrade or otherwise alter the operability of one or more core fibers, optical fibers that include redundant core fibers may maintain complete or partial functionality beyond the point of damage. As illustrated in FIG. 9A, the core fiber 137 ₂ is shown to be damaged within the cross-sectional region 220 ₂ while the core fibers 137 ₁ and 137 ₃-137 ₄ have not incurred damaged; thus, some functionality of the multi-core optical fiber 136 may be maintained via reflected signals received from the core fibers 137 ₁ and 137 ₃-137 ₄.

It should be understood that in instances in which the damage 904 is a complete break or fracture such that no incident light 155 propagates beyond the damage 904, the reflected light signals 906 ₁-906 ₄ do not exist.

While some particular embodiments have been disclosed herein, and while the particular embodiments have been disclosed in some detail, it is not the intention for the particular embodiments to limit the scope of the concepts provided herein. Additional adaptations and/or modifications can appear to those of ordinary skill in the art, and, in broader aspects, these adaptations and/or modifications are encompassed as well. Accordingly, departures may be made from the particular embodiments disclosed herein without departing from the scope of the concepts provided herein. 

What is claimed is:
 1. A method for placing a medical device into a body of a patient, the method comprising: providing a broadband incident light signal to an optical fiber included within the medical device, wherein the optical fiber includes a one or more core fibers, each of the one or more of core fibers including a plurality of reflective gratings distributed along a longitudinal length of a corresponding core fiber and each of the plurality of reflective gratings being configured to (i) reflect a light signal of a different spectral width based on received incident light, and (ii) change a characteristic of the reflected light signal for use in determining a physical state of the optical fiber; receiving reflected light signals of different spectral widths of the broadband incident light signal by one or more of the plurality of sensors; processing the reflected light signals associated with the one or more core fibers to identify at least one unexpected spectral width or a lack of an expected spectral width; determining whether damage has occurred to one or more of the core fibers based on identification of the at least one unexpected spectral width, a lack of an expected spectral width, or a reduction in intensity of a reflected light signal; determining a first core fiber affected by the damage; and determining a location of the damage along the first core fiber.
 2. The method of claim 1, wherein the at least one unexpected spectral width includes a spectral width not configured for use by any of the plurality of sensors of a core fiber.
 3. The method of claim 1, wherein the optical fiber is a single-core optical fiber.
 4. The method of claim 1, wherein the optical fiber is a multi-core optical fiber including a plurality of core fibers.
 5. The method of claim 4, wherein the damage affects a first subset of the plurality of core fibers.
 6. The method of claim 5, wherein a second subset of the plurality of core fibers is unaffected by the damage such that multi-core optical fiber maintains at least partial functionality based on the second subset of the plurality of core fibers.
 7. The method of claim 6, wherein the at least partial functionality includes one or more of fluctuation sensing of a distal tip of the medical device, shape sensing of the multi-core optical fiber, oximetry monitoring, distal tip confirmation, distal tip location detection, detection of entry of the distal tip of the medical device into an Azygos vein, impedance or conductance sensing, intravascular ECG monitoring or vessel cannulation detection.
 8. The method of claim 7, further comprising performing at least partial functionality of the multi-core optical fiber without considering information provided by a first core fiber that has reflected a light signal having a first unexpected spectral width.
 9. The method of claim 5, wherein the second subset of the plurality of core fibers includes redundant core fibers such that a shape sensing functionality of the multi-core optical fiber is maintained.
 10. The method of claim 3, wherein the medical device is one of an introducer wire, a guidewire, a stylet, a stylet within a needle, a needle with the optical fiber inlayed into a cannula of the needle or a catheter with the optical fiber inlayed into one or more walls of the catheter.
 11. The method of claim 3, wherein each of the plurality of sensors is a reflective grating, where each reflective grating alters its reflected light signal by applying a wavelength shift dependent on a strain experienced by the reflective grating.
 12. The method of claim 1, wherein determining the first core fiber is based on a unique identifier assigned to the first core fiber and association of unique identifier with each light signal reflected by the first core fiber.
 13. The method of claim 1, wherein determining the location of the damage includes identifying (i) a most distal sensor of the first core fiber from which a first light signal having an expected spectral width was received, and (ii) a most proximal sensor from which a second light signal having: (a) a first unexpected spectral width was received, (b) having a reduction in intensity was received, or (c) a corresponding expected spectral width was not received.
 14. The method of claim 1, wherein the logic, when executed by the one or more processors, causes further operations including generating an alert indicating that the optical fiber has been damaged.
 15. The method of claim 14, wherein the alert includes an indication of the location of the damage. 